Body communication antenna

ABSTRACT

An electromagnetic induction wireless communication system including: a magnetic antenna; an electric antenna; a tuning capacitor coupled to the magnetic antenna configured to tune the magnetic antenna; a controller configured to control the operation of the communication system; a signal source coupled to the controller configured to produce a communication signal used to drive the magnetic antenna and the electric antenna; a voltage control unit coupled to the signal source configured to produce one of an amplitude difference, phase difference, and an amplitude and a phase difference between the communication signal used to drive the magnetic antenna and electric antenna.

This application is a continuation-in-part of application Ser. No. 14/270,013, filed on May 5, 2014, which is hereby incorporated by reference for all purposes as if fully set forth herein. This application is also a continuation-in-part of application Ser. No. 14/302,791, filed on Jun. 12, 2014, which is hereby incorporated by reference for all purposes as if fully set forth herein.

TECHNICAL FIELD

Various exemplary embodiments disclosed herein relate generally to an electromagnetic induction radio.

BACKGROUND

There exist a variety of wireless systems which, illustratively, are used for short range distance communication. Some systems are used for communication around the human body; other systems may be used for communication in or around other objects. For example, currently RF based hearing aids are considered for wireless communication. Often such hearing aid systems operate in the 2.4 GHz ISM band. Such systems feature propagation by means of transversal waves, the magnetic and electric fields being in phase and covering a relatively large range of perhaps 30 meters. The large range may cause problems in terms of security of the communication content and may cause interference. Furthermore, because of their relatively high frequency of operation, such systems are heavily influenced by the human body. Somewhat more conventional hearing aids employ magnetic field induction as a wireless communication method. Unfortunately, magnetic field induction based wireless systems have a limited range if the antenna is comparatively small, such as would be required in a hearing aid. Not all parts of the human body can be reached with magnetic field induction-based systems with small antennas. Consequently, it can be difficult to provide communication between a hearing aid and a hand-held control using such systems.

SUMMARY

A brief summary of various exemplary embodiments is presented below. Some simplifications and omissions may be made in the following summary, which is intended to highlight and introduce some aspects of the various exemplary embodiments, but not to limit the scope of the invention. Detailed descriptions of an exemplary embodiment adequate to allow those of ordinary skill in the art to make and use the inventive concepts will follow in later sections.

Various exemplary embodiments relate to an electromagnetic induction wireless communication system including: a magnetic antenna; an electric antenna; a tuning capacitor coupled to the magnetic antenna configured to tune the magnetic antenna; a controller configured to control the operation of the communication system; a signal source coupled to the controller configured to produce a communication signal used to drive the magnetic antenna and the electric antenna; a voltage control unit coupled to the signal source configured to produce one of an amplitude difference, phase difference, and an amplitude and a phase difference between the communication signal used to drive the magnetic antenna and electric antenna.

Further, various exemplary embodiments relate to an electromagnetic induction antenna including: a capacitor having a first plate and a second plate spaced apart from the first plate; and an inductor including windings surrounding the first plate; wherein the capacitor and inductor are electrically connected, wherein the capacitor is an electric field antenna, and wherein the inductor is a magnetic field antenna.

Further, various exemplary embodiments relate to an electromagnetic induction antenna including: a first inductor including windings; a second inductor including windings spaced apart from the first inductor; and an impedance connecting the first and second inductors; wherein the first and second inductor form a capacitor; wherein the capacitor is an electric field antenna, and wherein the inductor is a magnetic field antenna.

Further, various exemplary embodiments relate to an electromagnetic induction wireless transceiver including: a magnetic antenna; and a signal source configured to produce a communication signal used to drive the magnetic antenna to produce electromagnetic induction fields, wherein the transceiver when connected to a first location on a body is configured to communicate with another electromagnetic induction wireless transceiver connected to a second location on the body.

Further, various exemplary embodiments relate to an electromagnetic induction wireless transceiver including: a magnetic antenna configured to receive an electromagnetic induction field, the magnetic antenna being connectable to a body; and a receiver configured to receive a communication signal carried by the electromagnetic induction fields, wherein the transceiver when connected to a first location on the body is configured to communicate with another electromagnetic induction wireless transceiver connected to a second location on the body

Further, various exemplary embodiments relate to an

BRIEF DESCRIPTION OF THE DRAWINGS

In order to better understand various exemplary embodiments, reference is made to the accompanying drawings, wherein:

FIG. 1 illustrates a block diagram of wireless communication system;

FIG. 2 illustrates a diagram of electrical and magnetic field lines during operation of the wireless communication system;

FIG. 3 illustrates the coupling capacitors CE1 and CE2 near a human body;

FIG. 4 illustrates block diagram of an embodiment of an electromagnetic induction radio;

FIG. 5 is a diagram illustrating comparative ranges of a communication system which uses magnetic field induction and a communication system using electromagnetic field induction;

FIG. 6 depicts a control and/or display unit;

FIG. 7 illustrates how the area around an antenna is divided into different regions;

FIG. 8 illustrates a prior art magnetic antenna;

FIG. 9 illustrates a prior art electric antenna;

FIG. 10 illustrates a first embodiment of a body communication antenna;

FIG. 11 illustrates the first embodiment of the body communication antenna mounted on an arm;

FIG. 12 illustrates a lumped model of the body antenna;

FIG. 13 illustrates the lumped model of the body antenna of FIG. 12 in a resonating transmitting circuit;

FIG. 14 illustrates a further embodiment where the body antenna may be extended with radio electronics;

FIG. 15 illustrates a second embodiment of a body communication antenna;

FIG. 16 illustrates a front view of a hearing aid H including the body antenna AS;

FIG. 17 illustrates a lumped model of the body antenna AS′

FIG. 18 illustrates the electrical equivalent model of the body antenna AS in a resonating transmitting circuit;

FIG. 19 illustrates another embodiment of the body antenna;

FIG. 20 illustrates a coil including successive nested coils with substantially the same shape with connectors;

FIG. 21 illustrates an embodiment of a wristband including body antennas;

FIG. 22 illustrates another embodiment of a wristband using a body antenna;

FIG. 23 illustrates the electric equivalent schematic of the body antenna in the wristband of FIG. 22;

FIG. 24 illustrates a remote control interacting with a hearing aid where the hearing aid uses an EIR radio;

FIG. 25 illustrates a bridging device receiving audio data from a TV using Bluetooth;

FIG. 26 illustrates a bridge device 2610 receiving audio data from a phone 2630 using Bluetooth;

FIG. 27 illustrates another embodiment of an EIR system; and

FIG. 28 illustrates simulation results comparing the received voltage in the EIR system of FIG. 27 with a MI system.

To facilitate understanding, identical reference numerals have been used to designate elements having substantially the same or similar structure and/or substantially the same or similar function.

DETAILED DESCRIPTION

The description and drawings illustrate the principles of the invention. It will thus be appreciated that those skilled in the art will be able to devise various arrangements that, although not explicitly described or shown herein, embody the principles of the invention and are included within its scope. Furthermore, all examples recited herein are principally intended expressly to be for pedagogical purposes to aid the reader in understanding the principles of the invention and the concepts contributed by the inventor(s) to furthering the art, and are to be construed as being without limitation to such specifically recited examples and conditions. Additionally, the term, “or,” as used herein, refers to a non-exclusive or (i.e., and/or), unless otherwise indicated (e.g., “or else” or “or in the alternative”). Also, the various embodiments described herein are not necessarily mutually exclusive, as some embodiments can be combined with one or more other embodiments to form new embodiments. As used herein, the terms “context” and “context object” will be understood to be synonymous, unless otherwise indicated.

An electromagnetic induction radio described herein improves the link budget and extends the communication range. The link budget is defined as,

${{{Link}\mspace{14mu} {{Budget}\mspace{14mu}\lbrack{dB}\rbrack}} = {20\; \log \; 10\left( \frac{V_{Rx}}{V_{Tx}} \right)}},$

where VTx is the transmitter voltage on the transmitter antennas and VRx is the received voltage on the receiver antennas.

In a related U.S. patent application Ser. No. 14/270,013 entitled “ELECTROMAGNETIC INDUCTION FIELD COMMUNICATION” filed on May 5, 2014 an electromagnetic communication method near a living body by means of a combination of a magnetic field and electric field with no intention to form transversal radiating waves is described. This results in a method that improves the link budget and extends the range to the complete living body and enables communication between devices near living bodies, including a first device connected to a first body and a second device connected to a second body such that the first device communicates with the second device, wherein the first and second bodies are connected through magnetic and electric near-field coupling. Even communication between more than two bodies is possible, but the embodiments described herein will use two living bodies for simplicity. Multiple devices with transceivers are also possible, but the embodiments described herein will use two devices or transceivers for simplicity.

The magnetic field is generated by a current through a first coil. The electric field can be generated by a first coupling capacitor, having a first conducting plate coupled to the body and a second conducting plate coupled to the environment. The wireless communication system is not galvanically connected to the ground. The magnetic and electric field can be received by a receiver at another place near the body by means of a second coil and a second coupling capacitor, the second capacitor having a first conducting plate coupled to the body and a second conducting plate coupled to the environment.

FIG. 1 illustrates a block diagram of the wireless communication system. FIG. 2 illustrates a diagram of electrical and magnetic field lines during operation of the wireless communication system. The wireless communication system of FIG. 1 includes a transmitter XMTR and receiver RCVR. Communication between transmitter XMTR and receiver RCVR is accomplished via a combination of an electric field and a magnetic field as will be further described. The transmitter XMTR and receiver RCVR are spaced apart from the human body HB by an exaggerated distance so that the electric field may be shown. The human body may be replaced by any other living body in FIG. 1, FIG. 2 and FIG. 3. Magnetic field H1 is generated by current through coil L1. An electric field E1 can be generated by a voltage on coupling capacitor CE1. Coupling capacitor CE1 has a first conducting plate coupled to the human body HB and a second conducting plate coupled to the environment as will be further illustrated below. Capacitors C1 and C2 are provided to resonate their respective circuits at the required operational frequency.

Magnetic field H1 and electric field E1 may be generated by the same voltage using sources S1 and S2. Accordingly, the sources S1 and S2 produce the communication signal to be transmitted. In this illustrative embodiment the sources S1 and S2 may generate a balanced voltage across the coil L1. However the voltage across the coil L1 may also be unbalanced and in this case only one source is required.

Magnetic field H2 and electric field E2 (which have different amplitudes than magnetic field H1 and electric field E1 respectively) may be received at a receiver RCVR positioned at another place near the human body (perhaps in the other ear) by means of a coil L2 and a coupling capacitor CE2. A signal detector A1 detects the signal received by the RCVR. Coupling capacitor CE2 has a first conducting plate coupled to the human body HB and a second conducting plate coupled to the environment as will be further illustrated in FIG. 3. Further, coils L1 and L2 have a mutual inductance M.

FIG. 1 shows an illustrative embodiment of a transmitter XMTR and receiver RCVR that allows uni-directional communication. In another embodiment, both XMTR and RCVR may be also transceivers and bi-directional communication is thus made possible.

Not illustrated in detail are the driving circuitry, signal processing circuitry, microphones, control circuitry, etc., although such items may be viewed as embodied in blocks denoted by CX or CR in FIG. 1.

This wireless communication system communicates using a wireless electromagnetic field communication method near a human body. The electromagnetic induction fields are a combination of a magnetic field H1 and electric field E1 with no intention to form transversal radiating waves. The magnetic field H1 is generated by a magnetic antenna, a coil L1, while the electric field E1 is generated by a voltage on a coupling capacitor CE1. This coupling capacitor CE1 has a first conducting plate P11 coupled to the human body HB and a second conducting plate P12 coupled to the environment. The wireless system, including the transmitter XMTR and receiver RCVR, is not galvanically connected to the ground. It will be noted that the electric field lines E1 and E2 extend down the length of the human body HB.

A combination of a magnetic field and an electric field is created, and the electric field is present between the living body and the environment. The magnetic induction field decreases with 60 db per decade distance from the source in air, however the electric induction field decreases with less than 60 db per decade of the distance from the source.

The magnetic field H2 and electric field E2 can be received by a receiver at another place near the human body by means of a coil L2 and a coupling capacitor CE2, the coupling capacitor CE2 having a first conducting plate P21 coupled to the human body and a second conducting plate P22 to the environment.

In the embodiments discussed, the coils and coupling capacitors are so small that (i.e. less than about 5% of the wavelength of the electric E1 and E2 and magnetic H1 and H2 fields), that there is not significant generation of undesired transverse radiating waves.

In an embodiment, coils L1 and L2 are unscreened and smaller (ideally much smaller) than the chosen wavelength of operation. The capacitors CE1 and CE2 each have one conducting surface, i.e., P11 and P22 in FIG. 3, which is close to or in contact with a body, illustratively, a human body HB. The opposing surfaces, i.e., plates P12 and P22 of FIG. 3 are closer to the environment than the human body HB, and the size of the plates are smaller (ideally much smaller) than the chosen wavelength of operation. Plates P12 and P11 are preferably parallel and have the same shape, but it is also permissible that the plates are of different size and only partially parallel (i.e. somewhat non-parallel) or side by side. The same is true for plates P21 and P22.

FIG. 3 illustrates the coupling capacitors CE1 and CE2 near a human body HB. The conductive plate P11 of coupling capacitor CE1 is coupled with the human body HB. The conductive plate P12 of coupling capacitor CE1 is coupled to the environment. The conductive plate P21 of coupling capacitor CE2 is coupled with the human body HB at another position. The conductive plate P22 of coupling capacitor CE2 is coupled to the environment. CE1 has a coupling factor CP1, and CE2 has a coupling factor CP2. The coupling factor CP1 and CP2 play a role in the link budget of the communication system.

Plates P11, P12, P21, and P22 may be made from conductive material, for example metal. In general, plates P11, P12, P21, and P22 may have a variety of shapes and may be surrounded by dielectric material so that the overall structure of CE1 and CE2 performs a capacitive function. In general, the dimensions of capacitors CE1 and CE2 should be small relative to the wavelength of operation.

However different applications may require a composition of electric and magnetic fields of different amplitudes and phase between them. Therefore a system is described below that may be integrated in a RF integrated circuit and that is suitable to generate a blending of field amplitudes and phase that may be programmed to be specifically suited for various applications. The blending can be continuously adaptable. In order to understand the effects of different amplitudes and phases between the electric and magnetic fields various tests and measurements were done. The results of these tests are discussed below and provide insight as to the benefits of varying the amplitudes and phases between the electric and magnetic fields.

By way of an example embodiment, if capacitors CE1 and CE2 are approximately 10 pF in value (which is somewhat defined by coupling capacitor design), while coils L1 and L2 are be approximately 3.7 μH, then some extra capacitance may be required to tune the circuit to the desired operational frequency, for example 10.6 MHz. Consequently the values of capacitors C1 and C2 are approximately 50.96 pF. In an embodiment, capacitors C1 and C2 are a capacitor bank which may be integrated into an RF integrated circuit that is adjustable to resonate at the required frequency. The adjustability compensates for the added capacitance due to the human body.

From measurements it was found that the link budget for the electromagnetic induction system can be changed. Different link budget values can be obtained by means of varying the phase and amplitude of the magnetic and the electric field that is generated by the wireless communication system. Thus a system that varies the amplitude and phase of the voltage applied to the coil antenna and the capacitor antenna may be used to improve the performance of the wireless communication system.

FIG. 4 illustrates block diagram of an embodiment of an electromagnetic induction radio. The electromagnetic induction radio (EIR) may include a digital processing unit DPU, signal processing units SPU1 and SPU2, signal generators S1 and S2, buffers B1, B2, and B3, a tuning capacitor TC, a voltage processing unit VC/PS, an magnetic antenna coil MA, and an electric antenna capacitor EA.

The digital processing unit DPU may control the operation of the EIR and processes the signals related to the communication. The digital processing unit may contain analog digital converters (ADC) and/or digital analog converters (DAC), memory, storage, and all the hardware and software required to process the communication signals. The digital processing unit may include a processor that may be any hardware device capable of executing instructions stored in a memory or other storage or otherwise processing data. As such, the processor may include a microprocessor, field programmable gate array (FPGA), application-specific integrated circuit (ASIC), or other similar devices. The memory may include various memories such as cache or system memory. As such, the memory may include static random access memory (SRAM), dynamic RAM (DRAM), flash memory, read only memory (ROM), or other similar memory devices. The storage may include one or more machine-readable storage media such as read-only memory (ROM), random-access memory (RAM), magnetic disk storage media, optical storage media, flash-memory devices, or similar storage media. In various embodiments, the storage may store instructions for execution by the processor or data upon with the processor may operate. For example, the storage may store a base operating system for controlling various basic operations of the hardware. It may also store data received and processed by the EIR. Also, the storage my include instructions used to process the data received by the EIR.

Signal processing units SPU1 and SPU2 may contain the required hardware to interface to the antenna circuitry MA and EA and the digital processing unit DPU. SPU1 and SPU2 may include a processor that may be any hardware device capable of executing instructions stored in a memory or other storage or otherwise processing data. As such, the processor may include a microprocessor, a signal processor, graphics processor, field programmable gate array (FPGA), application-specific integrated circuit (ASIC), or other similar devices. The signal processing unit SPU1 may help implement the transmitter function while the signal processing unit SPU2 may help implement the receiver function. In such a case the EIR may have a transceiver functionality and thus may be able to perform bidirectional communication.

In a transmitter mode, the magnetic field Um is generated by a first alternating current I_(m) through a magnetic antenna, coil MA, while the electric field Ue is generated by a second alternating voltage V_(e) on the electric antenna capacitor EA. The current I_(m) through the coil MA is dependent on the voltage on the coil:

I _(m) =V _(m) /Z _(coil),

Z _(coil)=2πfL _(coil)

The two voltages V_(m) and V_(e) thus define the magnetic and electric fields Um and Ue respectively. Changing one of the amplitudes of V_(m) and V_(e) or the phase between them, changes the combination of the magnetic field Um and electric field Ue and thus blending of the fields may be done in order to improve the performance of the wireless communication system.

Signal processing unit SPU1 may command signal generators S1 and S2 to produce currents that drive the resonating circuit formed by coil MA and tuning capacitor TC. Accordingly, the sources S1 and S2 produce the communication signal to be transmitted. In this illustrative embodiment the sources S1 and S2 may generate a balanced voltage across MA. However the voltage across MA may also be unbalanced and in this case only one source is required. TC is an integrated capacitor bank that may be adjusted by the digital processing unit DPU to tune the receiver/transmitter. The resonating frequency can be chosen in one of the industrial, scientific, and medical (ISM) bands, for example 10.6 MHz. The resonating circuit may have a bandwidth that is sufficient for the required communication mode data rate. Optionally the bandwidth may be adapted by means of inserting additional loss in the resonating circuit using, for example, a resistor bank which may have an adjustable resistance. This may be an additional functional block in the EIR.

The voltage V_(m) on the magnetic antenna MA is processed in the voltage processing unit VC/PS and further applied to the electric antenna EA. The VC/PS produces a voltage V_(e) that is applied to the electric antenna EA. The VC/PS may reduce or increase the input voltage V_(w) relative to V_(m). The VC/PS may additionally also change the phase between V_(m) and V_(e). In this way the composition of magnetic and electric fields may be changed according to the needs of the application. Alternatively the voltage Ve that is applied to the electric antenna EA is processed in the voltage processing unit VC/PS and further applied to the magnetic antenna MA. The VC/PS produces a voltage Vm that is applied to the magnetic antenna MA. The VC/PS may reduce or increase the input voltage V_(m) relative to V_(e). The VC/PS may additionally also change the phase between V_(e) and V_(m). In this way the composition of magnetic and electric fields may be changed according to the needs of the application.

In the receive mode the voltage received by the magnetic antenna MA may be combined with the voltage received by the electric antenna EA. Before combining both signals the phase and/or amplitude between them may be adapted.

For example, when both signals are combined in a parallel tuned circuit, the amplitude of the induced antenna voltages should have a 180 degree phase shift between them to generate an optimal combined output signal. This may not always be desirable for all applications due to antenna design and positioning at the human body. Moreover the phase between them may change dynamically and the VC/PS may continuously respond to such changes.

The signal processing unit SPU2 may process the received voltages from the antennas MA and EA. It is noted that the VC/PS may have bidirectional functionality. The signal at the resonating circuit formed by TC and MA may be buffered by buffers B2 and B3. An additional buffer B1 may be available to monitor the difference between received magnetic and electric field strength. Alternatively, the receiver and transmitter can also have separate receive and transmit VC/PS.

The DPU may adjust the amplitude and phase characteristics between the electric and magnetic fields used to implement communication between a transmitter and a receiver. Information regarding the communication environment may be based upon various collected test data. Also, test measurements may be made for each individual user of the communication system. Further, various channel measurement signals may be included as part of the communication signal in order to determine variations in the communication channel during the operation of the wireless communication system. These channel measurements may then be used to adjust the phase and amplitude between the magnetic and electric fields. Further, feedback loops may be used to further monitor and adjust the phase and amplitude of between the magnetic and electric signals.

The EIR may be implemented as a combination of different integrated circuits (ICs) or on a single IC. Further, the DPU, SPU1, and SPU2 are shown as separate physical and functional blocks in FIG. 4, but the DPU, SPU1, and the SPU2 may be implemented in a single processor which may be its own IC. Also, SPU1 and SPU2 may be implemented on a single signal processing unit which may be its own IC. The DPU or the combination of the DPU, SPU1, and SPU2 may be called a controller that controls the operation of the EIR.

FIG. 5 is a diagram illustrating comparative ranges of a communication system which uses magnetic field induction and a communication system. In FIG. 5, the horizontal axis indicates directivity when coils L1 and L2 are coaxial; the vertical axis indicates directivity when coils L1 and L2 are parallel. The directivity in case of a link using the magnetic field induction method is illustrated by line 511. It will be noted that the range drops significantly when moving from the case where both coils are coaxial to the case where coils are parallel. Using the diagram of FIG. 5, if the transmit coil L1 of FIG. 1 were located at the origin 519 of FIG. 5, one can see that the receiver coil L2 can be placed in either location 521 or 523 (which correspond, respectively, to a coaxial orientation with respect to the transmitter coil L1 or a parallel orientation with respect to transmitter coil L1) and best-case detection of the magnetic field generated by transmit coil L1 will be achieved. However, if the receiver coil L2 is positioned along a line which is oriented at forty five degrees between locations 521 and 523, (i.e. at location 525), the receiver coil must be placed substantially closer to the transmitter coil L1 for adequate detection to occur. The disclosed embodiment, however exhibits a more omnidirectional range profile and possibly greater range. The omnidirectional profile and possibly greater range in case of a link using electromagnetic induction fields facilitate more robust communication.

In another embodiment, there may be a separate control and/or display unit. FIG. 6 depicts a control and/or display unit 611. Control and/or display unit 611 has two plates 613 and 615 on opposite sides. Control and/or display unit 611 may be held in the hand of a user. One of the plates, 613 or 615 will be held more securely in the hand than the other and will therefore be more strongly coupled to the user's body, while the other plate will have a somewhat stronger coupling to the environment. Control and/or display unit 611 is capable of communicating with transmitter XMTR or receiver RCVR. Illustratively, control and/or display unit may, in combination, or individually, provide: volume control; noise reduction control; human body parameters such as heart rate, and other items such as physical parameters monitored around the body. Operation of the control and/or display unit is facilitated by the electromagnetic induction fields. In an embodiment, dimensioning and parallelism are similar to that described for plates P12 and P22 above. Control and/or display unit may have a display, and internal circuitry, 619, similar to either transmitter XMTR or receiver RCVR (or may have internal circuitry which is a transceiver as previously described).

Now embodiments of antennas that may be used with in the EIR will be described.

As described above, many wireless communications occur in the far-field region, where information is transferred through the radiation of electromagnetic waves. While radiating electromagnetic waves in the far-field sufficiently address the need for communication over larger distances, it may not be an effective solution for short range body communication. When body communication over very short distances is required, often it is difficult to limit the electromagnetic transmitted signal to within close proximity of the transmitter.

Further, as described above, near-field communication has been seen as an efficient technique for limited range communication. The amplitude of near-field electromagnetic waves decreases faster than far-field electromagnetic waves as it travels through the channel. This results in very limited communication range.

While far-field refers to the region around a radiating antenna in which electromagnetic waves are radiated into space, the term near-field describes a region close to the transmitting antenna in which non-radiating magnetic waves exist. The boundary between the near-field and far-field region is not fixed and it changes with the operating frequency. The boundary between the near and far-field region may be defined using transmission range, wave impedance or phase variation of radiation.

FIG. 7 illustrates how the area around an antenna is divided into different regions. The two main regions are near-field and far-field. In the far-field region, the electromagnetic waves that propagate are a combination of electric and magnetic waves. An electromagnetic wave consists of an electric field and a magnetic field, which are perpendicular to each other and also to the direction of propagation.

However, the near-field region includes two sub-regions: the reactive and radiating region. In the radiating region, the angular field distribution depends on distance, while in the reactive zone energy is stored and not radiated. The precise boundary between these two regions may be determined based on the specific application. The reactive near-field range may be defined by r<λ2π, where r is range and λ, is wavelength. For example, near-field communication in the 10.6 MHz frequency range results is a reactive near-field zone of 4.5 meters. This example shows that communication on the human body at this frequency occurs in the reactive near-field by means of induction.

Communication in the near-field can occur through the use of electric field, magnetic field, or both as described above. Electric and magnetic waves have different behavior in the near-field region. One of the main differences is that there is a need for specific antenna types for data transmission using each field type. Electric field transmission occurs by using an electric antenna such as a dipole or whip while magnetic field transmission occurs by using a magnetic antenna such as a loop antenna.

FIG. 8 illustrates a prior art magnetic antenna. This type of antenna is often used, for example, in magnetic induction based hearing aids. The generated magnetic field in transmit mode is increased by means of the ferrite core.

FIG. 9 illustrates a prior art electric antenna. This type of antenna is often used in portable applications and may include either a whip or a dipole.

FIG. 10 illustrates a first embodiment of a body communication antenna. This first embodiment of the body antenna 1000 may generate and receive electromagnetic induction fields as described above. In contrast with antennas for wireless communication that occurs in the far-field region, this body antenna 1000 is not always power matched. The body antenna 1000 may include a magnetic field generating inductor 1010 and electric field generating capacitor including capacitor plates 1020, 1030. The body antenna 1000 may be further included in a series or parallel resonant circuit as described above. Components of the antenna or resonant circuit may be part of an integrated circuit with radio functionality.

The inductor 1010 may be planar but this is not required as it may be designed to conform to the shape of a device including the body antenna 1000. The inductor 1010 includes windings that are wrapped around the capacitor plate 1020. The inductor 1010 may include two connectors 1050, 1060 that may be connected to other devices. The winding will include a conductive material. The windings may be formed using various known techniques. For example, the windings may be formed on a dielectric substrate 1040 that may be a part of the body antenna 1000. The dielectric substrate 1040 may be made of for example, paper, plastic, or some other non-conductive material.

The capacitor plates 1020, 1030 may be positioned at a specific distance from one another to form the capacitor. The capacitor plates 1020, 1030 may be planar but this is not required as the capacitor plates 1020, 1030 may be designed to conform to the shape of a device including the body antenna 1000. Both capacitor plates are electrically conductive. The capacitor plates 1020, 1030 may include connectors 1070, 1080 respectively. The inductor 1010 may be connected via connectors 1050, 1060 to the connectors 1070, 1080 of the capacitor plates 1020, 1030.

In a variation of the embodiment of the body antenna 1000 of FIG. 10, the capacitor plate 1020 may be eliminated. Then the inductor 1010 may form a capacitor along with the capacitor plate 1030. Further, the inductor 1010 may continue to wind into the center. The dimensions of the inductor 1010 may be selected to correspond to the dimensions of the capacitor plate 1030 in order to provide an adequate capacitance. Further, while the inductor and capacitor plates are shown as rectangular, they may be other shapes such as square, circular, oval, elliptical, or any other polygon.

FIG. 11 illustrates the first embodiment of the body communication antenna 1000 mounted on an arm 1100. FIG. 12 illustrates a lumped model of the body antenna 1000. The inductor 1010 connections 1050, 1060 are electrically connected to the connections 1080, 1070 respectively of the capacitor plates 1020, 1030.

FIG. 13 illustrates the lumped model of the body antenna 1000 of FIG. 12 in a resonating transmitting circuit. A tuning capacitor 1090 and a signal source 1095 may be connected to the body antenna 1000 and causes the antenna to resonate in the required frequency band. The capacitor C2 may be an integrated capacitor bank in a RF communication integrated circuit (IC). The inductor 1010 may have inductance values in the 1-8 μH range. Further, the capacitor formed by the capacitor plates 1020, 1030 may have capacitance values 1 to 50 pF range.

FIG. 14 illustrates a further embodiment where the body antenna 1000 may be extended with radio electronics. The radio electronics 1410 may be embedded in the first plate 1020 or second plate 1030 of the capacitor. The feeding connections of the antenna are connected to the input of the radio electronics 1410.

FIG. 15 illustrates a second embodiment of a body communication antenna. The body antenna AS may include two coils L1 and L2 and an impedance Z1 connected between the coils L1 and L2. The two coils L1 and L2 that are a distance D separated from each other. The coils L1 and L2 may each be attached to a side of a wireless product and may follow its contours. Such contours may be flat or curved. Both coils L1 and L2 may generate or receive magnetic induction fields. The two coils L1 and L2 form inductors. The coils L1 and L2 may be formed of a conductive material using any known technique. The coils may be formed on a dielectric substrate (not shown) that may be made of for example, paper, plastic, or some other non-conducting material. The two coils L1 and L2 also form a capacitor that will be described in further detail below.

The first coil L1 is connected to the second coil L2 by means of the impedance Z1. The first coil L1 and the second coil L2 may be connected in such a way that the total inductance is the sum of the inductance of L1 and the inductance of L2, assuming the connection impedance Z1 does not include any significant inductance.

FIG. 16 illustrates a front view of a hearing aid H including the body antenna AS. The first coil L1 is attached to or formed on the front side of the hearing aid H. The second coil L2 is attached to or formed on the back side (not shown) of the hearing aid H. The separation between the two coils D is defined by the thickness of the hearing aid product H.

The attachment of the coils to the wireless product may be done using various methods. It may be by a plastic carrier having the coils or the coils may be printed with conductive material. There is no restriction as long as the coil is constructed from conductive material. The shape of the coils may be selected to fit the shape of the end product. It may follow the contour of the wireless product housing.

FIG. 17 illustrates a lumped model of the body antenna AS. The first coil L1 and the second coil L2 are connected by means of the impedance Z1 to form an effective inductor having an inductance larger than the inductance of coil L1 or L2. The connection impedance Z1 may include a discrete component and may be used to adapt the total inductance/impedance to the required value. The impedance may include resistive, capacitive, or inductive elements in any combination as needed.

Due to the physical separation D between the two coils L1 and L2, a capacitor C1 is formed. The capacitance value of the capacitor C1 may be determined as follows:

C=∈o×∈r×A/D,

where C is capacitance in farads, A is the surface area of one coil, D is the distance between the coils, ∈o is the permittivity of free space, 8.854×10⁻¹² F/m, and ∈r is the relative permittivity of the material between the coils.

A voltage source, V_(source), connected to a capacitor generates an electrical field. The electric field strength in the near field zone, in an air environment, can be found by differentiating the field potential V_(source) with respect to the distance r which is defined for a dipole by:

${V_{source} = \frac{P}{4\; \pi \; ɛ\; r^{3}}},$

where V_(source) is the voltage across the coils, P is the dipole moment, ∈ is the permittivity of the material between the coils, and r is the distance from the coils.

The dipole moment P is estimated by approximating the coils as a parallel plate capacitor with a distance D between the plates:

P=Q×D,

where P is the dipole moment, Q is the charge on the coils, and D is the distance between the coils. Calculating the resulting charge Q on the coils can be done by the relationship:

Q=C×V _(source).

FIG. 18 illustrates the electrical equivalent model of the body antenna AS in a resonating transmitting circuit. The tuning capacitor C2 value connected to the body antenna AS causes the antenna to resonate in the required frequency band. The capacitor C2 may be an integrated capacitor bank in a RF communication IC. The value of the resistor R may be selected so that the required bandwidth of the resonating circuit results in high quality communication. The resistor R may be an integrated resistor bank in a RF communication IC.

FIG. 19 illustrates another embodiment of the body antenna. The only difference of the body antennas in FIG. 15 and FIG. 19 is the shape of the coils. In FIG. 15 the coils are in a triangular shape, and in FIG. 19 the coils are in a rectangular shape. Further, any coil shape (for example, circular, oval, elliptical, or any polygon) may be used that provides the desired inductance value. The coils may form a spiral. Alternatively, the coil may include successive nested coils with substantially the same shape with connectors as illustrated in FIG. 20. Further, the coils may conform to the shape of the wireless body product.

FIG. 21 illustrates an embodiment of a wristband including body antennas. Any of the body antenna embodiments described above may be used in FIG. 21. In FIG. 21, both coils, L1 and L2 may be attached to each side of a non-conductive wristband W. If the body antenna of FIG. 10 is used then the capacitive plate 1020 and coil 1010 may be on one side of the wristband and the capacitive plate 1030 may be on the other side of the wristband.

FIG. 22 illustrates another embodiment of a wristband using a body antenna. In this second wristband, four coils L1, L2, L3 and L4 used and are connected via impedance Z1 to form a larger inductance. This results in two capacitors C1 and C2 formed by the four coils that are able to generate or receive electric fields.

FIG. 23 illustrates the electric equivalent schematic of the body antenna in the wristband of FIG. 22. As shown, the four coils L1, L2, L3, and L4 are in series and form to capacitors C1 and C2 connected in parallel.

The body antenna AS has been evaluated by the construction of an ear-bud product intended to be worn in the ear canal. The ear-bud acted as the receiver. The ear-bud has dimensions of 10 by 10 by 3 mm. At both front and back side of the ear-bud a coil is attached. Each coil has an inductance of 1 uH. The capacitance between the coils is 0.8 pF. Both coils are connected in series with a connection impedance of 0 ohms and tuned with a tuning capacitor C2 to a desired resonance frequency.

Measurements show that such an antenna system has a gain of 6 db in sensitivity receiving electric and magnetic fields versus receiving only magnetic induction field.

Now a few applications of the above described EIR system using the body antennas will be described below. In the use cases below a traditional magnetic induction (MI) radio in a hearing aid is replaced by an EIR. MI systems require the use of relatively large ferrite coils as the antennas, thus restricting how small the hearing aid may be. Further, MI communication is very sensitive to coil orientation. Accordingly, in remote or bridge devices two orthogonal coils are used to increase the chance of successful communication. This increases size, cost, and complexity of the remote or bridge device. In some solutions, the coil may be integrated into a neck loop of the remote or bridge device. This strap is in plain sight and may create privacy issues for the hearing aid user.

Hearing aids have historically made use of magnetic induction (MI) radio for communication between a hearing aid and an external device such as a remote control or a bridge device. FIG. 24 illustrates a remote control 2410 interacting with a hearing aid 2420 where the hearing aid 2420 uses an EIR radio. A remote control device 2410 may be used by the hearing aid wearer to change settings such as, e.g., volume and the selected program of the hearing aid 2420. The communication between the remote control device 2410 and the hearing aid 2420 may use electromagnetic induction communication.

A bridge device bridges communication between the hearing aid and some other audio source for example. The bridge device supports various use cases. FIG. 25 illustrates a bridging device 2510 receiving audio data from a TV 2530 using Bluetooth. The bridge device 2510 then forwards the audio data to the hearing aids 2520 using EIR communication.

FIG. 26 illustrates a bridge device 2610 receiving audio data from a phone 2630 using Bluetooth. The bridge device 2610 then forwards the audio data from the phone 2630 to the hearing aid 2620 using EIR radio communication. Additionally, microphone data from either the hearing aid 2620 or from a microphone in the bridge device 2610 is transmitted wirelessly to the phone 2630 in a similar fashion.

The use of EMI communication between a hearing aid and a remote or bridge device may provide various benefits including the following benefits. An EIR may provide a substantially better link budget than an MI radio (for example, up to 30 dB) for on-body communication. As a result, the transmit power of the external device may be lowered accordingly, resulting in increased battery lifetime and/or smaller batteries. Because lower transmit powers translate into lower transmit voltages this in turn also potentially removes the need for a discrete power amplifier as the voltage levels become more compatible with CMOS technology. This also implies that a symmetric link may be established between hearing aid and the remote control which simplifies the communication and allows the remote control to read back information from the hearing aid.

FIG. 27 illustrates another embodiment of an EIR system. The EIR system includes a transmitter 2705 in communication with a receiver 2710. This transmitter 2705 is similar to the transmitter XMTR in FIG. 1, except that it uses only a coil 2715 for its antenna. The coil 2715 is coupled to a source 2755 similar to sources S1 or S2 in FIG. 1. The source 2755 may drive a current through antenna coil 2715 and generating a magnetic field that is passed through the body 2735 with the same attenuation as in air because the magnetic permeability μ is the same for the human body bio material as for air. The magnetic field is attenuated by the 3rd power of the distance, which is an attenuation of 18 db per doubling of the distance. The body 2735 may be positioned on a floor 2740 which may be conductive or not.

The coil 2715 is positioned close to the human skin and may make contact or not. The coil 2715 generates a magnetic field 2750. The magnetic field 2750 generates an electric field 2745 with a direction perpendicular to the body 2735. This electric field is bound to the human body 2735. As a result an electric field 2745 is available around the body 2735. The receiver 2710 may receive and detect this electric field 2745.

The electric field may induce weak currents 2730 in the body 2735. The electric field 2745 may be measured around and on the whole body 2735 and is strongest near the coil 2715. The electric field 2745 is attenuated less than magnetic field 2750 along the body. However the irregular shape of the body along a transmission path may provide additional attenuation. This is different compared with a transmission path in air where the electric field is attenuated with the 3rd power of the distance.

Coil 2715 can be any design. Such design may be made to produce as strong of a magnetic and electric field as possible within the physical constraints of the device implementing the transmitter 2705. A larger coil may produce a larger magnetic and electric field. Further, a planar coil may produce a larger magnetic and electric field than a coil using a magnetic core. The increase in electric field may be due to the capacitance between the adjacent windings of the coil. Further, larger voltages across the coil will produce stronger magnetic and electric fields.

The receiver 2710 is similar to the receiver RCVR in FIG. 1. It receives the magnetic field 2750 and electric field 2745 generated by the coil 2715. Thus the transmitter 2715 produces induction fields including magnetic fields 2750 and electric fields 2745 close to the body that may be received the receiver 2710 at another place at the body. As previously described, these induction fields may be received by the receiver 2710 using two antennas. The first antenna which is a coil 2720 is sensitive to the magnetic field 2750, and the second which is a capacitor 2725 is sensitive to the electric field 2745. The signals from both antennas may be combined in an efficient way to establish a communication link budget that is superior to a magnetic induction (MI) system. The operation of the receiver 2710 is similar to the operation of the receiver RCVR in FIG. 1.

FIG. 28 illustrates simulation results comparing the received voltage in the EIR system of FIG. 27 with a MI system.

In the EIR system, a ferrite coil of 9 mm long and a diameter of 2 mm was used as the transmitter antenna. This sort of hearing aid coil is used today in a behind the ear application. The coil is positioned 2 mm from the skin of a human.

Two receiver antennas were positioned at another position at the human body. The electric sensitive antenna is a capacitor with rectangular plates of 20×20 mm and 4 mm separation. The magnetic sensitive antenna was a ferrite coil of 9 mm long and a diameter of 2 mm like that used as the transmitter antenna. Both electric and magnetic antennas are combined in a parallel resonance circuit and the relative received voltage as recorded as shown in FIG. 28. Further, voltages for the MI system were recorded as well as also shown in FIG. 28. It can be seen that the received voltage according the EIR system is always higher as compared with the art magnetic induction system.

Thus by not having the capacitor plates in the EIR system 2700 space is saved. Further, while the performance of the EIR system 2700 of FIG. 27 is not quite as good as the performance of the EIR system of FIG. 1, such decreased performance may be acceptable in applications where space is a premium. Further, two-way communication is still possible with the EIR system 2700. The communication performance in the two different directions will not be the same, but in certain applications such asymmetry may be acceptable.

Accordingly, an EIR communication system is still possible where the one of the transmitter/receiver uses only a coil for an antenna as long as the other transmitter/receiver using both a coil and a capacitor. This still allows for communication around a body. Further, the use of EIR improves performance over a system that only use one of the fields.

For all of the EIR embodiments described above, the EIR embodiments are much less sensitive to the relative orientation of both antennas than MI radio. Hence, the use of multiple coils in the external device to provide antenna diversity may be avoided while still having robust communication under all circumstances and orientations.

Also, efficient EMI antennas may be constructed without making use of ferrite rod-based coils but by simple planar wound coils and capacitance plates as described above. This may reduce the required antenna volume and allows for further miniaturization of the remote device. Additionally, it avoids the use of expensive ferrite rods.

All of the benefits mentioned above allow for external devices that may be substantially smaller and/or be built in new form factors. One particularly attractive embodiment for a bridge device or a remote control could be in the form of an elegant smart watch, which may be worn inconspicuously around the wrist hence protecting the privacy of the hearing aid wearer.

Another important use case for the above described EIR system using the body antennas involves the binaural use case where audio from the one hearing aid is transmitted to the other hearing aid and vice versa. This allows the hearing aids to perform audio beam forming, resulting in increased intelligibility of sounds for the hearing aid user. Support of binaural communication has however been limited mostly so far to so-called behind-the-ear (BTE) devices because of size restrictions and small batteries. MI communication requires large ferrite rod MI antennas that cannot be used in in-the-ear (ITE) or in-the-canal (ITC) hearing aids. Further, MI transmission requires instantaneous current spikes that cannot be supplied by small batteries used in ITE and ITC devices.

The application of EIR to ITE and ITC hearing aids will result in effective communication between the EIR or ITE hearing aids. Because of the lower power requirements and the ability to build small and effective body antennas, binaural communication between ITE and ITC hearing aids is possible.

Although various embodiments described relate to a method of communicating near a living body, propagating objects other than a living body may be used in the described embodiments. The first and a second device may be connected through magnetic and electric near-field coupling using the propagating objects to help propagate the fields.

It should be appreciated by those skilled in the art that any block diagrams herein represent conceptual views of illustrative circuitry embodying the principles of the invention. Further, in the circuits shown additional elements may also be included as needed, or variations to the structure of the circuit may be made to achieve the same functional results as the circuits illustrated.

Although the various exemplary embodiments have been described in detail with particular reference to certain exemplary aspects thereof, it should be understood that the invention is capable of other embodiments and its details are capable of modifications in various obvious respects. As is readily apparent to those skilled in the art, variations and modifications can be effected while remaining within the spirit and scope of the invention. Accordingly, the foregoing disclosure, description, and figures are for illustrative purposes only and do not in any way limit the invention, which is defined only by the claims. 

What is claimed is:
 1. An electromagnetic induction antenna comprising: a capacitor having a first plate and a second plate spaced apart from the first plate; and an inductor including windings surrounding the first plate; wherein the capacitor and inductor are electrically connected, wherein the capacitor is an electric field antenna, and wherein the inductor is a magnetic field antenna.
 2. The antenna of claim 1, further comprising a tuning capacitor coupled to the capacitor and the inductor to create a resonating circuit that operates at a specific frequency.
 3. An electromagnetic induction wireless transceiver comprising: the electromagnetic induction antenna of claim 1; and a signal source configured to produce a communication signal used to drive the electromagnetic induction antenna to produce electromagnetic induction fields, wherein the transceiver when connected to a body is configured to communicate with another electromagnetic induction wireless transceiver connected to the body.
 4. The transceiver of claim 3, further comprising a voltage control unit coupled to the signal source configured to produce one of an amplitude difference, phase difference, and an amplitude and a phase difference between the communication signals used to drive the magnetic field antenna and electric field antenna.
 5. The transceiver of claim 4, further comprising a controller including a data processing unit and signal processing unit, wherein the controller controls the operation of the voltage control unit.
 6. A hearing aid comprising: the electromagnetic induction antenna of claim 1; and a signal source configured to produce a communication signal used to drive the electromagnetic induction antenna to produce electromagnetic induction fields, wherein the hearing aid when connected to a body is configured to communicate with another hearing aid connected to the body.
 7. The hearing aid of claim 6, further comprising a receiver connected to the electromagnetic induction antenna configured to receive a communication signal from the other hearing aid connected to the body.
 8. A hearing aid comprising: the electromagnetic induction antenna of claim 1; and a receiver connected to the electromagnetic induction antenna configured to receive a communication signal from another hearing aid connected to the body.
 9. A hearing aid comprising: the electromagnetic induction antenna of claim 1; and a receiver connected to the electromagnetic induction antenna configured to receive a communication signal from a bridging device near the body, wherein the communication signal includes audio data from a remote device in communication with the bridging device.
 10. The hearing aid of claim 9, further comprising a signal source configured to produce a communication signal used to drive the electromagnetic induction antenna to produce electromagnetic induction fields, wherein the hearing aid when connected to a body is configured to transmit the communication signal to the bridging device connected to the body.
 11. A hearing aid comprising: the electromagnetic induction antenna of claim 1; and a receiver connected to the electromagnetic induction antenna configured to receive a communication signal from a remote control device near the body, wherein the operation of the hearing aid is configured to be controlled by the communication signal received from the remote control.
 12. The hearing aid of claim 11, further comprising a signal source configured to produce a communication signal used to drive the electromagnetic induction antenna to produce electromagnetic induction fields, wherein the hearing aid when connected to a body is configured to transmit the communication signal to the remote control device connected to the body.
 13. A wrist mounted device comprising: the electromagnetic induction antenna of claim 1; and a signal source configured to produce a communication signal used to drive the electromagnetic induction antenna to produce electromagnetic induction fields, wherein the wrist mounted device when connected to a body is configured to communicate with another device connected to the body.
 14. The wrist mounted device of claim 13, further comprising a receiver connected to the electromagnetic induction antenna configured to receive a communication signal from the other device connected to the body.
 15. A wrist mounted device comprising: the electromagnetic induction antenna of claim 1; and a receiver connected to the electromagnetic induction antenna configured to receive a communication signal from another device connected to the body.
 16. A wrist mounted device comprising: a first electromagnetic induction antenna of claim 1; a second electromagnetic induction antenna of claim 1 connected in parallel to the first electromagnetic induction antenna; and a signal source configured to produce a communication signal used to drive the first and second electromagnetic induction antennas to produce electromagnetic induction fields, wherein the wrist mounted device when connected to a body is configured to communicate with another device connected to the body.
 17. The wrist mounted device of claim 16, further comprising a receiver connected to the first and second electromagnetic induction antennas configured to receive a communication signal from the other device connected to the body.
 18. A wrist mounted device comprising: a first electromagnetic induction antenna of claim 1; a second electromagnetic induction antenna of claim 1 connected to the first electromagnetic induction antenna; and a receiver connected to the first and second electromagnetic induction antennas configured to receive a communication signal from another device connected to the body. 